(12) INTERNATIONAL APPLICATION PUBLISHED UNDER THE PATENT COOPERATION TREATY (PCT) (19) World Intellectual Property Organization International Bureau (10) International Publication Number (43) International Publication Date . 19 April 2012 (19.04.2012) WO 2012/050945 Al (51) International Patent Classification: CA, CH, CL, CN, CO, CR, CU, CZ, DE, DK, DM, DO, A61K 31/198 (2006.01) A61P 11/00 (2006.01) DZ, EC, EE, EG, ES, FI, GB, GD, GE, GH, GM, GT, A61K 33/06 (2006.01) A61P 11/10 (2006.01) HN, HR, HU, ID, IL, IN, IS, JP, KE, KG, KM, KN, KP, A61K 33/14 (2006.01) A61K 9/00 (2006.01) KR, KZ, LA, LC, LK, LR, LS, LT, LU, LY, MA, MD, ME, MG, MK, MN, MW, MX, MY, MZ, NA, NG, NI, (21) International Application Number: NO, NZ, OM, PE, PG, PH, PL, PT, QA, RO, RS, RU, PCT/US201 1/053833 RW, SC, SD, SE, SG, SK, SL, SM, ST, SV, SY, TH, TJ, (22) International Filing Date: TM, TN, TR, TT, TZ, UA, UG, US, UZ, VC, VN, ZA, 29 September 201 1 (29.09.201 1) ZM, ZW. (25) Filing Language: English (84) Designated States (unless otherwise indicated, for every kind of regional protection available): ARIPO (BW, GH, (26) Publication Language: English GM, KE, LR, LS, MW, MZ, NA, RW, SD, SL, SZ, TZ, (30) Priority Data: UG, ZM, ZW), Eurasian (AM, AZ, BY, KG, KZ, MD, 61/387,855 29 September 2010 (29.09.2010) US RU, TJ, TM), European (AL, AT, BE, BG, CH, CY, CZ, PCT/US201 1/049435 DE, DK, EE, ES, FI, FR, GB, GR, HR, HU, IE, IS, IT, 26 August 201 1 (26.08.201 1) US LT, LU, LV, MC, MK, MT, NL, NO, PL, PT, RO, RS, SE, SI, SK, SM, TR), OAPI (BF, BJ, CF, CG, CI, CM, (71) Applicant (for all designated States except US): PUL- GA, GN, GQ, GW, ML, MR, NE, SN, TD, TG). MATRIX, INC. [US/US]; 99 Hayden Avenue, Lexing ton, Massachusetts 02421 (US). Declarations under Rule 4.17 : — as to applicant's entitlement to apply for and be granted (72) Inventors; and a patent (Rule 4.1 7(H)) (75) Inventors/ Applicants (for US only): LIPP, Michael M. [US/US]; 45A Flanagan Drive, Framingham, M as — as to the applicant's entitlement to claim the priority of sachusetts 01701 (US). SUNG, Jean C. [US/US]; 259 the earlier application (Rule 4.17(Hi)) Putnam Avenue, Cambridge, Massachusetts 02139 (US). Published: (74) Agents: UNDERWOOD, Robert H. et al; McDermott — with international search report (Art. 21(3)) Will & Emery LLP, 28 State Street, Boston, Mas sachusetts 02109 (US). — before the expiration of the time limit for amending the claims and to be republished in the event of receipt of (81) Designated States (unless otherwise indicated, for every amendments (Rule 48.2(h)) kind of national protection available): AE, AG, AL, AM, AO, AT, AU, AZ, BA, BB, BG, BH, BR, BW, BY, BZ, © © © (54) Title: CATIONIC DRY POWDERS (57) Abstract: The invention relates to respirable dry particles that contain one or more divalent metal cations, such as calcium, in ¾ an amount of less than 3% by weight, and to dry powders that contain the respirable particles. The dry particles can further contain S an active agent, or can be used as carrier particles to deliver an active agent. Cationic Dry Powders RELATED APPLICATIONS [0001] This application claims the benefit of U.S. Provisional Application No. 61/387,855, filed on September 29, 2010 and PCT/US 11/49435, filed on August 26, 201 1, the entire teachings of these applications are incorporated herein by reference. BACKGROUND OF THE INVENTION [0002] Pulmonary delivery of therapeutic agents can offer several advantages over other modes of delivery. These advantages include rapid onset of drug action, the convenience of patient self-administration, the potential for reduced drug side-effects, ease of delivery, the elimination of needles, and the like. With these advantages, inhalation therapy is capable of providing a drug delivery system that is easy to use in an inpatient or outpatient setting. [0003] Metered dose inhalers (MDIs) are used to deliver therapeutic agents to the respiratory tract. MDIs are generally suitable for administering therapeutic agents that can be formulated as solid respirable dry particles in a volatile liquid under pressure. Opening of a valve releases the suspension at relatively high velocity. The liquid then volatilizes, leaving behind a fast-moving aerosol of dry particles that contain the therapeutic agent. MDIs are reliable for drug delivery to the upper and middle airways but are limited because they typically deliver only low doses per actuation. However, it is the bronchioles and alveoli that are often the site of manifestation of pulmonary diseases such as asthma and respiratory infections. [0004] Liquid aerosol delivery is one of the oldest forms of pulmonary drug delivery. Typically, liquid aerosols are created by an air jet nebulizer, which releases compressed air from a small orifice at high velocity, resulting in low pressure at the exit region due to the Bernoulli effect. See, e.g., U.S. Pat. No. 5,51 1,726. The low pressure is used to draw the fluid to be aerosolized out of a second tube. This fluid breaks into small droplets as it accelerates in the air stream. Disadvantages of this standard nebulizer design include relatively large primary liquid aerosol droplet size often requiring impaction of the primary droplet onto a baffle to generate secondary splash droplets of respirable sizes, lack of liquid aerosol droplet size uniformity, significant recirculation of the bulk drug solution, and low densities of small respirable liquid aerosol droplets in the inhaled air. [0005] Ultrasonic nebulizers use flat or concave piezoelectric disks submerged below a liquid reservoir to resonate the surface of the liquid reservoir, forming a liquid cone which sheds aerosol particles from its surface (U.S. 2006/0249144 and U.S. 5,551,416). Since no airflow is required in the aerosolization process, high aerosol concentrations can be achieved, however the piezoelectric components are relatively expensive to produce and are inefficient at aerosolizing suspensions, requiring active drug to be dissolved at low concentrations in water or saline solutions. Newer liquid aerosol technologies involve generating smaller and more uniform liquid respirable dry particles by passing the liquid to be aerosolized through micron-sized holes. See, e.g., U.S. Pat. No. 6,131,570; U.S. Pat. No. 5,724,957; and U.S. Pat. No. 6,098,620. Disadvantages of this technique include relatively expensive piezoelectric and fine mesh components as well as fouling of the holes from residual salts and from solid suspensions. [0006] Dry powder inhalation has historically relied on lactose blending to allow for the dosing of particles that are small enough to be inhaled, but aren't dispersible enough on their own. This process is known to be inefficient and to not work for some drugs. For example, the drug loading in the overall dry powder is low due to the presence of the lactose carrier which is typically large and bulky. Several groups have tried to improve on these shortcomings by developing dry powder inhaler (DPI) formulations that are respirable and dispersible and thus do not require lactose blending. Dry powder formulations for inhalation therapy are described in U.S. Pat. No. 5,993,805 to Sutton et al; U.S. Pat. No. 6,9216527 to Platz et al; WO 0000176 to Robinson et al; WO 9916419 to Tarara et al; WO 0000215 to Bot et al; U.S. Pat. No. 5,855,913 to Hanes et al; and U.S. Pat. Nos. 6,136,295 and 5,874,064 to Edwards et al. [0007] Broad clinical application of dry powder inhalation delivery has been limited by difficulties in generating dry powders of appropriate particle size, particle density, and dispersibility, in keeping the dry powder stored in a dry state, and in developing a convenient, hand-held device that effectively disperses the respirable dry particles to be inhaled in air. In addition, the particle size of dry powders for inhalation delivery is inherently limited by the fact that smaller respirable dry particles are harder to disperse in air. Dry powder formulations, while offering advantages over cumbersome liquid dosage forms and propellant-driven formulations, are prone to aggregation and low flowability which considerably diminish dispersibility and the efficiency of dry powder-based inhalation therapies. For example, interparticular Van der Waals interactions and capillary condensation effects are known to contribute to aggregation of dry particles. Hickey, A. et al., "Factors Influencing the Dispersion of Dry Powders as Aerosols", Pharmaceutical Technology, August, 1994. [0008] The propensity for particles to aggregate or agglomerate increases as particle size decreases. In order to deaggregate particles of a smaller size, a relatively larger dispersion energy is needed. This can be described as inhaled flowrate dependency since the degree of dispersion of the agglomerated particles is a function of inhaled flowrate. What this means to a clinician and a patient is that the dose the patient receives varies depending on their inspiratory flowrate. [0009] One example of how the art has dealt with the need for a high dispersion energy is to require the patient to inhale on a passive dry powder inhaler (DPI) at a high inspiratory flow rate. In Anderson, et al, (European Respiratory Journal, 1997, Nov; 10(1 1):2465-73) micronized sodium chloride was delivered to patients to cause broncho-provocation. Patients were required to breathe forcefully on the DPI in order to receive the broncho-provocative dose. Flowrates of greater than or equal to 50 LPM on a standard DPI and greater than 28 LPM on a high-resistance DPI were required, both produce higher dispersion energies.